Hydrogels for localized chemotherapy of liver cancer: a possible strategy for improved and safe liver cancer treatment

Abstract The systemic drug has historically been preferred for the treatment of the majority of pathological conditions, particularly liver cancer. Indeed, this mode of treatment is associated with adverse reactions, toxicity, off-target accumulation, and rapid hepatic and renal clearance. Numerous efforts have been made to design systemic therapeutic carriers to improve retention while decreasing side effects and clearance. Following systemic medication, local administration of therapeutic agents allows for higher ‘effective’ doses with fewer side effects, kidney accumulation, and clearance. Hydrogels are highly biocompatible and can be used for both imaging and therapy. Hydrogel-based drug delivery approach has fewer side effects than traditional chemotherapy and can deliver drugs to tumors for a longer time. The chemical and physical flexibility of hydrogels can be used to achieve disease-induced in situ accumulation as well as subsequent drug release and hydrogel-programmed degradation. Moreover, they can act as a biocompatible depot for localized chemotherapy when stimuli-responsive carriers are administrated. Herein, we summarize the design strategies of various hydrogels used for localized chemotherapy of liver cancer and their delivery routes, as well as recent research on smart hydrogels.


Introduction
Liver cancer, the world's leading cause of cancer death and the fifth leading cause in the USA is the only one of the top five most lethal cancers to see an annual percentage increase in occurrence (Miller et al., 2019). Hepatocellular carcinoma (HCC) contributes to 80-90% of all primary liver cancers in adults, while cholangiocarcinoma (CCA) accounts for 10-15% (Ringelhan et al., 2018). Children and adolescents are also affected by liver cancer, with hepatoblastoma (HB) and HCC accounting for 67-80% and 20-33% of cases, respectively (Sharma, 2020). Globally, the number of newly diagnosed cases and the age-standardized incidence rate of liver cancer have increased over the last few decades, despite substantial public health efforts to combat this problem. Liver diseases are more prevalent in developing countries (Starley et al., 2010) and risk factors include fatty liver disease, hepatitis B and C viruses, alcohol-related cirrhosis, obesity, smoking, diabetes, iron overload, and numerous dietary exposures (Center & Jemal, 2011). Despite this, various de novo cases in non-cirrhotic patients have invalidated the theory that it only occurs in cirrhotic livers. HCC has also been reported in patients who did not have any signs of cirrhosis and had no histological evidence of hepatitis (Mittal et al., 2016;Pennisi et al., 2019). Liver cancer has a poor prognosis. Only small proportion of patients (almost 5-15%) are candidates for surgical removal and appropriate for earlystage patients only with impaired hepatic regenerative capacity, usually without cirrhosis; right hepatectomy has a higher risk of post-operative complications than left hepatectomy. The following are some treatments available for more advanced stages: (a) trans-arterial chemoembolization (TACE), which improves 2-year survival for intermediate-stage HCC patients by 23% when compared to conservative therapy. (b) Sorafenib oral dosing, a kinase inhibitor that is the most commonly prescribed treatment for late-stage cancers. However, the treatment benefits only about a third of patients, and drug resistance develops in six months of starting the regimen (El-Serag et al., 2008). Chemotherapeutic drugs, like sorafenib, can cause toxicity and/or drug inefficacy if used over an extended period of time. Therefore, current ablation and chemotherapy treatments are ineffective toward improved prognosis of this deadly disease. More research is needed to discover improved techniques to treat liver cancer.
Chemotherapy, which employs highly toxic chemotherapeutic chemicals against cancer cells, is the preferred therapeutic method for various cancer managements because of its superior efficacy (Qin et al., 2017). Although there are significant limitations to systemic chemotherapy, it is the most often employed therapeutic approach. It entails administering anti-cancer medications intravenously at maximal tolerable levels, which causes significant toxicity to healthy cells ranging from neutropenia to cardiomyopathy (Scharovsky et al., 2009). Furthermore, systemic chemotherapy is inefficient at delivering drugs to therapeutic concentrations at target sites, and maintaining appropriate drug concentrations within tumors is difficult (Jang et al., 2003). Hence, only a small fraction of the injected amount reaches the tumor site, resulting in decreased therapeutic potential and increased damage to healthy cells. Hence, the use of localized delivery in cancer therapy has increased. Localized delivery can be defined as a way of delivering a drug from a dosage form to a specific location inside the biological system where the maximum pharmacological impact is desired. Ye et al. incorporated polylactic acid microspheres carrying epirubicin into collagen film intra-tumoral administration. The mouse liver cancer model showed significantly increased tumor suppression upon intra-tumoral implantation of microspheres compared with epirubicin delivered intra-tumorally alone (De Souza et al., 2010). This review is focused on localized chemotherapy either via intratumoral injection or the delivery of therapeutics in close proximity to the tumor site(s). Drug accumulation at target sites significantly reduces their systemic exposure and is considered a key factor for minimum toxicity and maximum efficacy. In this regard, biomaterials would be beneficial for keeping the drug at the targeted sites (Figure 1).
Hydrogels are polymer networks with a hydrophilic character that are three-dimensionally crosslinked. They can easily swell in water and retain a huge amount of water while swollen. They can change volume dramatically under the influence of a wide range of physical, chemical, and biological stimuli. Temperature, electric field, magnetic field, solvent composition, pressure, light, and sound are all examples of physical stimuli, whereas pH, ions, and specific molecular recognition events are all examples of chemical or biological stimuli (Qiu & Park, 2001;Miyata et al., 2002). In this regard, hydrogel would be considered safe with improved efficacy in cancer treatment of the liver. Hydrogels have become a hot topic in recent years, with about 5000 papers published in 2010, which is nearly five times the amount of papers published in 2010 linked to 'nanotechnology', also lately become a most focused area in the scientific community . Hydrogels prevalence is due to four characteristics: biocompatibility, biodegradability, loading capacity of drug entity, and controlled release profile. Biocompatibility suggests that the hydrogels are not associated with significant cellular or systemic toxicity in the body upon its implantation, and are not included in stimulating the immune system. Moreover, many of the polymers used to make hydrogels for cancer therapy are biodegradable, including natural polymers and synthetic polymers (e.g. chitosan (CTS) (Jamal et al., 2018), hyaluronic acid (HA) (Cho et al., 2015), alginate (ALG) (Shih et al., 2018), polyesters , and polyphosphazene (PPZ) (Society, 2018)) which are rapidly depleted by cells and remodeled in the body after administration (Yamaguchi et al., 2007). US Patent 5,514,380 describes the use of nontoxic and biodegradable hydrogel based on multi-block copolymers as drug delivery vehicles. They were made from a biodegradable, hydrophobic hard block and a hydrophilic soft block. The hydrolysis of intramolecular amide and ester bonds, which occurs naturally in the human body, could be used to degrade them. Copolymers PEO and polypropyleneoxide (PPO) and/or polyethyleneoxide (PEO) with 600-30,000 Da of molecular weight (MW) have essential properties for the hydrophilic, non-biodegradable polymers used in the aforementioned patent. In this regard, polyglycolide (PGA), polylactide (PLA), or a PLA/PGA copolymer are being used as biodegradable polymers (Song et al., 1996). Additionally, hydrogels, due to their porous nature, can carry huge content of water-soluble substances, i.e. peptides and proteins (Vermonden et al., 2012). Additionally, the release rate of drugs can be regulated by altering the structure of hydrogels (Sepantafar et al., 2017).
Hydrogels are large polymeric networks that are highly magnified, hydrophilic, and capable of retaining a large amount of water within their pores (Martin & Youssef, 2018;Wang, 2018). Due to their enhanced biocompatibility, these bioactive resources are commonly used in tissue engineering (Vermonden & Klumperman, 2015). Hydrogels have a porous structure and soft surface and behave similarly to natural living tissues. Owing to various stimuli-responsive potential to temperature, pH, pressure, electric and magnetic fields, these hydrogels are undoubtedly referred to as smart materials. Even at a slight pH change in the swelling medium, these materials have a high potential for proton release and uptake . The above mention characteristic of hydrogels makes them able to be served as an effective drug delivery vehicle. Literature has demonstrated the remarkable contributions of multi-responsive hydrogels such as polyvinyl alcohol crosslinked polyacrylamide and poly(N-isopropylacrylamide) (PNIPAM)/CTS as smart sensors, effectors, and targeted delivery to tumor cells Manga & Jha, 2017). Polymeric hydrogels such as CTS and keratin (polylactic keratin) are extensively studied for their potential use in the fabrication of LCD (liquid crystal display) and OLED (organic light-emitting diode) materials, as well as specific drug delivery systems (Karimi et al., 2017).
Although hydrogels vary greatly in shape and size, drug release behavior are similar due to analogous interactions between polymer networks and drugs. When compared to normal tissue, various distinct features found in tumor tissues (e.g. hypoxia, enhanced retention, and permeability effects as well as acidic pH) can be utilized to design drug carriers (Danhier et al., 2010). In general, cancer treatment hydrogels can be designed in a variety of sizes, ranging from nanogels to macroscopic gels (Yallapu et al., 2011), as well as injectable hydrogels (in situ) (Norouzi et al., 2016), and can be developed to demonstrate multiple drug mechanisms in external and internal stimuli. In this paper, various types of hydrogels and their administration routes for liver cancer treatment will be discussed and we review various drug release behavior and hydrogel formation and measure the efficacy of hydrogels as a controlled drug carrier and their future prospects.

Advantage of hydrogels in drug delivery
Various definitions have been proposed for hydrogels over the years and are frequently described as a cross-linked polymeric network formed via conjugation or reaction of one or more monomers and possess water-swollen characteristics. Though, hydrogels are three-dimensional networks having potential for water absorption because of the existence of hydrophilic functionalities capable to fill the space between macromolecules and possess enhanced affinity toward biological fluids (Chai et al., 2017). Hydrogel-based advanced dressings have been shown to be ominously effective toward wound healing because of their moisture maintaining potential at the application site, preventing fluids from spreading to other healthy skin areas. Various hydrogels are now available commercially, including DermaFilm V R , Condress V R , Kaltostat V R , and Sofargen V R (Tavakoli & Klar, 2020), with some containing ingredients such as zinc or iodine ions, which have cleansing and antimicrobial properties, respectively (Cal o & Khutoryanskiy, 2015).
Drug delivery is one application where hydrogels special physical properties have gained attention. Controlling crosslink density in the gel matrix and affinity of hydrogels for the aqueous environment can be used to fine-tune their highly porous structure (Schiller & Lai, 2020). This allows drugs to be loaded into their gel matrix and then released in an amount that is dependent on the diffusion coefficient of small molecules or macromolecules. Due to their pharmacokinetic properties, it is possible to use hydrogels for drug delivery that is primarily focused on maintaining a high local concentration of the drug in the surrounding tissues for an extended period, while they can also be used for systemic delivery. Due to their biocompatibility, hydrogels can be used in the peritoneum and other areas of the body (Sultana et al., 2019). Hydrogels high-water content, as well as their physicochemical similarity to the natural extracellular matrix and mechanical properties, improves biocompatibility. It is possible to develop hydrogels that are biodegradable or dissolvable via environmental, hydrolytic, or enzymatic pathways, although this may not be desirable regarding the time and placement of the drug delivery device. Hydrogels, on the other hand, are somewhat pliable and may be molded to fit any surface. The muco-or bio-adhesive characteristics of some hydrogels can be helpful in the application of these hydrogels on non-horizontal surfaces or in the immobilization of these hydrogels at the application site. Rosiak et al. utilized gamma radiation to cross-link natural polymers (e.g. agar or gelatin) and synthetic polymers (e.g. poly(vinyl pyrrolidone) (PVP) or poly(vinyl alcohol) (PVA)) to produce sterile hydrogels for wound treatment. Their hydrogels are currently manufactured and marketed under the brand names 'Kikgel' and 'Aqua-gel' wound dressings (Rosiak et al., 1989). Hydrogels are being patented for contact lenses, in addition to the wound dressing. When macromonomers are used to make hydrogels, the necessity for their purification may be eliminated, because the used materials are generally nontoxic. For the synthesis, pH-sensitive polymers were used (hydroxyethyl)methacrylate-co-methacrylic acid, allowing for the production of hydrogels capable of undergoing a volume phase transition at a particular pH. This can be done by using salt solutions like sodium phosphate or sodium bicarbonate in the device in order to change the microenvironment and initiate the release of active ingredient. This solution's pH might be anywhere from 7.5-8.4 or 6.4-7.3, which could cause the hydrogel to either expand or contract (Rosenthal et al., 2006).
As hydrogels have been successfully used in various biomedical applications, it was hypothesized that they have the potential to be drug delivery platforms in cancer therapy. In cases of nonsquamous or incompletely removed tumors, local drug administration may be extremely beneficial even though most cancer treatment research focuses on systemic and oral administration. In this frame of reference, the in situ application of hydrogels, particularly stimuli-responsive hydrogels, at the tumor site/cavity has already been postulated, to promote local sustained drug release while reducing off-target effects and systemic exposure (Puente et al., 2018). Furthermore, using depot systems reduces the need for multiple cycles for cancer therapy, which has several negative consequences for patients as well as a financial impact on healthcare systems (Wei et al., 2020). Hydrogels that respond to various stimuli like temperature, light, pH, magnetic fields, and ionic strength are promising smart materials . US Patent 8,383,153 B2 demonstrates a drug carrier based on poly(amidoamine) based hydrogel. This temperature-and pH-sensitive hydrogel possessed a structure designed for prolonged drug release rather than burst release. The substance can be synthesized in a single step by connecting the secondary amine groups (NH) of a diamine molecule (such as piperazine) and vinyl groups (CH 2 CH) of an alkylene bisacrylamide compound. This hydrogel can be employed as a vehicle for a variety of physiologically active compounds via diverse administration routes . Such kind of hydrogel has received prominence due to the possibility of manipulating the hydrogel's rheological behavior in response to the various conditions of the tumor microenvironment. Indeed, cancer cells exhibit a variety of metabolic adaptive responses to ensure their survival. Nutrient and glucose uptake, lactic acid production under aerobic circumstances, and adaptation to hypoxic and microenvironments containing less amount of nutrient are just a few of them. In addition, cancer cells have a low pH extracellular environment and a high pH intracellular cytoplasm (Persi et al., 2018). As a result of these characteristics, it is possible for the design of delivery carrier with stimuli-responsive behavior for tumor-targeting (Table 1).
Numerous hydrogel-based formulations have been developed over the years for cancer prevention, diagnosis, and treatment, with several of them being enrolled in clinical trials. Additionally, several have received European Medicines Agency (EMA) and/or FDA approval and have been promoted to clinical practice such as Lupron V R depot or Eligard V R , two hydrogels based on PLGA for in situ delivery of leuprolide acetate to treat prostate cancer of advanced stage (Wei et al., 2020). TraceIT V R is another example. It is a microparticle of PEG hydrogel covalently bound with iodine that has been approved as a tissue marker. Once injected, it enables precise tumor visualization via computed tomography (CT), magnetic resonance imaging (MRI), and ultrasound, allowing for a more precise cancer cells identification prior to surgery. Additionally, it is also helpful to identify more precise dose selection in radiation therapy, thereby avoiding normal sites. The product maintains its dimensional stability for three months before being completely absorbed after six months (Bair et al., 2015). TraceIT V R 's feasibility and efficacy as an organ spacer are being evaluated in clinical trials for vaginal or prostate sparing, rectal cancer treatment, and also as a spacer in pancreatic cancer patients between their pancreas and duodenum (Andrade et al., 2021). SpaceOAR V R , a PEGbased hydrogel is another example of an organ spacer approved by the FDA for use in preventing rectum injury during the session of radiation therapy in patients with prostate cancer (Velde et al., 2019).

Classification of hydrogels
Classification of hydrogel has been reported on the various basis including the following.

Classification according to the source
Two different categories of hydrogels are present according to their natural or synthetic origins (Zhao et al., 2013).

Classification based on the composition of the polymer
Some major hydrogel classes are formed as a result of the preparation method. Following are the example of these: a. Homopolymeric hydrogels: Monomers are the fundamental constituents of polymer networks, and homopolymeric hydrogels are networks composed entirely of a single monomer species (Iizawa et al., 2007). Crosslinked structures can be found in homopolymers depending on the nature of their monomer and the method used for polymerization. b. Copolymeric hydrogels: Copolymeric hydrogels are composed of two or more distinct monomer species that contain at least one hydrophilic component. The polymer network may have a random, block, or alternating configuration (Yang et al., 2002). c. Multipolymer interpenetrating polymeric hydrogel (IPN), a type of hydrogel, is composed of two independent cross-linked synthetic and/or natural polymer components held together in a network form. One component of semi-IPN hydrogel is a cross-linked polymer, while the other is a non-cross-linked polymer (Maolin et al., 2000).

Configuration-based classification
Hydrogels can be classified depending on their structure and composition as follows: amorphous (non-crystalline), crystalline, and semicrystalline (a complex blend of crystalline and amorphous phases).

Classification according to the nature of the cross-linking
Hydrogels are classified into two types based on the chemical or physical cross-linked junctions. Permanent junctions exist in chemically cross-linked networks, whereas transient junctions occur in physical networks as a result of entanglements of the polymer chain or physical interactions such as hydrogen bonds, ionic interactions, or hydrophobic interactions (Hacker et al., 2019).

Classification according to network electrical charge
There are four types of hydrogels based electrical charges on the cross-linked chains including nonionic, ionic amphoteric electrolyte, and zwitterionic hydrogels ( Figure 2).

Synthesis of hydrogel
From a wide range of monomeric and polymeric constituents, hydrogels are produced such as acrylamide    (Sahraei & Ghaemy, 2017), gums (Ding et al., 2018), cellulose and rice husk (Gharekhani et al., 2017). Generally, the preparation of hydrogels utilizes either synthetic or natural polymers. When compared to conventional hydrogels, crosslinked junction hydrogels have unique and improved properties such as electrical, thermal, variable MW specific functionality with desired chemical content, and mechanical properties. Alginate-methylcellulose hydrogels that have been blended and cross-linked have shown to be promising materials for encapsulating and delivering olfactory unsheathing cells (OECs). They can be successfully used as a promising system for cell delivery owing to their highest encapsulation potential (Surrao et al., 2020). Electrostatic interactions between two naturally occurring polysaccharides, CTS, and HA resulted in polyelectrolyte multilayers and macroscopic hydrogels. Self-healing properties have been reported in such polyelectrolyte complexes, which can be used in biomedical applications (Barroso et al., 2019). Interpolymer complexes are formed as a result of the association between these poly-ions, which are regulated by specific bonding systems such as electrostatic interaction and hydrogen bonding between distinct polymer chains. Hydrogels are divided into two groups based on the types of cross-link junctions: chemically cross-linked and physically cross-linked.

Synthesis of physically cross-linked hydrogel
In physically cross-linked hydrogels, ionic/electrostatic interactions, hydrogen bonding, amphiphilic polymers self-assembly, crystallization, interactions of protein, and metal  coordination are the key physical interactions between polymer chains . For example, polyacrylic and polymethacrylic acids form hydrogen-bonded complexes with PEG. They are formed only when carboxylic acid groups undergo protonation, resulting in pH-sensitive hydrogel formation (Siqueira et al., 2018). Alginate is also a natural polymer that forms a gel when it comes into contact with divalent cations, for example, Ca 2þ or Mg 2þ . Thermally induced phase transitions in amphiphilic polymers, such as poloxamers, result in hydrogel formation owing to hydrophobic interactions occurring above the lower critical solution temperature (LCST) (Russo & Villa, 2019). Hydrogels based on PVA are an example of physical crosslinking induced by crystallization, as polymer undergoes crystallization and gelation as a result of repeated freeze-thaw of a solution (Kumar & Han, 2017). The main disadvantage of hydrogels obtained via physical crosslinking is their potential lack of or compromised stability under physiological environments. Therefore in vivo application, chemical crosslinking is preferred (Siqueira et al., 2018).

Synthesis of chemically cross-linked hydrogel
Due to the covalent linkages between the polymeric chains, chemically crosslinked hydrogels exhibited remarkable mechanical properties and were found to be more durable under physiological. Additionally, their degradation behavior is controllable, even though it is typically irreversible. In comparison to physically cross-linked hydrogels, a potential disadvantage is the frequent requirement of catalysts and organic solvents, which commonly generate concerns regarding biocompatibility and environmental influence . Click chemistry, which includes the formation of Schiff base, photopolymerization, Michael addition or Diels-Alder reaction, reversible addition-fragmentation chain transfer (RAFT) polymerization, free radical polymerization (FRP), or enzyme-catalyzed reactions, is commonly used to promote covalent bonds in chemically cross-linked hydrogels . Owing to the existence of certain groups in the hydrophilic polymers such as COOH-, NH2-, and OH-, isocyanate-OH/NH 2 reaction, the formation of amine-carboxylic acid, or Schiff base is frequently used to covalently link polymers together to form the network of the hydrogel. Schiff base is a chemical compound that is frequently used in the formation of hydrogels and is typically formed when amines react nucleophilically with the electrophilic carbon of ketones or aldehydes. For instance, glycol CTS has been reported to be cross-linked with PEG, which led to the formation of promising hydrogels to deliver anticancer drugs . Due to the existence of unsaturated groups, acrylate derivatives (e.g. glycidylmethacrylate (GMA) and PEG diacrylate (PEGDA)) are frequently used as pre-polymers in photopolymerization cross-linking. Photo-initiators (visible or UV light) such as Irgacure 2959, or Eosin-Y, among others, react with these groups. Under the influence of light, photons cleave photoinitiators, generating free-radical which in turn react with the vinyl bonds of pre-polymer, thereby facilitating crosslinking between the polymer chains (Sultana et al., 2019). For example, a transglutaminase enzyme catalyzes the reaction between the -carboxamide group (glutamine modified PEG) and the '-amine' group resulting in the formation of an amide bond, which can be used to make PEG-based hydrogels (

Hydrogels for localized chemotherapy of liver cancer
Different techniques and approaches are used for liver cancer patients depending on their diagnosis and stage which include chemotherapy, surgery, radiation and immunotherapy, gene therapy and targeted therapy (Bykov et al., 2018;Senft et al., 2018). Among these approaches, chemotherapy is critical for tumor control and recurrence prevention. Chemotherapeutic medicines' anti-tumor action kills tumor cells by causing drug toxicity (Zhou et al., 2017). Additionally, chemotherapeutic drugs that were directly injected into a tumor undergo frequent removal from the blood circulation, implying that the drugs could not be accumulated in tumor tissue for an extended time, defeating the goal of tumor elimination (Wang et al., 2015). Chemical medications may harm normal tissues as well as malignant cells if they are not selective or targeted. Traditional chemotherapeutic medications are acquiring new life due to the invention of the hydrogel. Therefore, several chemotherapeutic agents are encapsulated in hydrogel and injected into the tumor site to prolong the drug's content in the tumor tissue, minimize systemic toxicity, and prevent the discomfort of multiple injections (Takimoto & Awada, 2008). Hydrogels are an efficient drug delivery strategy because of the presence of an excess of water and the network of cross-linked polymer that has excellent biocompatibility, low cytotoxicity, and a high capacity for drug encapsulation (Li & Mooney, 2016) and have thus been widely used in recent years for cancer treatment (Fang et al., 2018;. Drugs are administered directly into the tumor or near to it through the hydrogel (Pan et al., 2018 Hydrogels have gained interest as a depot for local drug delivery over the last decade, particularly in restricted and localized pathology. Based on amine aldehyde chemistry, a unique class of biocompatible and biodegradable adhesive hydrogels has been prepared . Aldehydes derived from dextran macromolecules provide adhesion via causing interaction with tissue amines, whereas unreacted aldehydes undergo reaction with dendrimer's amines to generate material cohesive bulk. Nonreactive dextran aldehyde crosslinks with dendrimer amines, lowering the free aldehyde content, preventing attachment to other organs, and forming the hydrogel's cohesive bulk. Researchers investigated how endogenous triggers alter the structure and characteristics of hydrogels in both in vitro and in vivo Zhang et al., 2021). Additionally, research was also conducted regarding the possibility of using this structure as a nanoparticle depot for triggered cargo release (Deng et al., 2021;Li et al., 2022). A design of rational hydrogel that combines specific stimuli sensing which results in situ assembly of hydrogel, prompted hydrogel disintegration, and triggered release of drug from embedded cargo NPs, all of which can result in on-demand therapeutic effects. This section will describe our research on tissue-and disease-responsive dendrimer-dextran hydrogels and will provide insight into how to build materials that impart local therapeutic effects ondemand.

Thermosensitive hydrogels
Another stimuli-responsive hydrogel, thermosensitive hydrogels, have been developed most frequently in recent years. Due to a low LCST, over which gels transition occurs to a gel state while remaining in the solution form. Thus, a hydrogel with an LCST between body and room temperature is ideal for in situ gelations after injection. Numerous polymers with thermosensitive characteristics have been employed to date, including PNIPAM having the capability to undergo sol-gel transition at 32 C of LCST or lower when hydrophobic groups are introduced (Yoshida et al., 1995). Elastin-like polypeptides (ELPs), synthetic polypeptides, have a controllable LCST ranging from 0 to 100 C (Meyer & Chilkoti, 1999). In regards to thermo-responsive hydrogels, there has been an increase in interest in combining thermal sensitivity with other stimuli-responsive features in order to obtain more effective delivery, such as thermal/pH dual sensitive hydrogels and thermal-magnetic dual sensitive hydrogels (Khan et al., 2019;Nandwana et al., 2019;Ruan et al., 2019). Additionally, the loading of drugs in hydrogels has evolved from a single therapeutic agent to co-loading with other new therapeutic agents, most notably cytokines, antibodies, and genes (Lv et al., 2018;. In comparison to the past usage of exclusively in situ injections, administration routes have become more diverse, for example, the use of transdermal patches (Makhmalzadeh et al., 2018). Aside from the functional behavior of thermosensitive hydrogels, release kinetics was also investigated at various temperatures and the precise control of the release behavior was determined by altering the hydrogel porosity (Danyuo et al., 2019) (Figure 4). Wan et al. (2016) described the co-assembly of DOX and nanomedicines (D-PNAx) to produce temperature-sensitive PNAx triblock polymers for localized liver cancer chemotherapy (Wan et al., 2016). Through intratumoral delivery of D-PNAx nanomedicines combined with thermal-sensitive in situ hydrogels formation, good anticancer efficacy against H22 tumors was demonstrated. By simply combining doxorubicin hydrochloride and PNAx polymers, D-PNAx nanomedicines displayed significant entrapment efficacy. The controlled release trend of D-PNA100 nanomedicines demonstrated only 9.4% release of DOX in a single day and 60% over 10 days. D-PNA100 nanomedicines demonstrated remarkable anticancer effectiveness against H22 tumors when administered intratumorally. The primary limitations of systemic chemotherapy for HCC are the low accumulation of the anticancer drug in tumors and their systemic toxicity. Thermoresponsive hydrogels are well-suited for the efficient local administration of chemotherapeutics at the same time. Gao et al. developed an in situ injectable hydrogel system with thermosensitive features for intratumoral administration of norcantharidin-loaded nanoparticles (NCTD-NPs) and DOX to HCC tumors (Gao et al., 2021). The synthesized drugloaded hydrogel displayed excellent thermal sensitivity, remaining liquid at room temperature but immediately transforming into a non-flowing gel upon exposure to body temperature, and sustained the release of the drugs. In vitro experiments demonstrated that the hydrogel loaded with drugs was significantly more antiproliferative than the free drugs in HepG2 cells. Antitumor assays in an animal model have shown that the hydrogel effectively inhibited tumor growth, reduced adverse effects, and prolonged survival in mice carrying H22 tumors compared with other groups. Additionally, immunohistochemistry staining demonstrated that the drug-loaded hydrogel group had considerably lower levels of Ki-67 and CD31 expression than the other groups (p < .05), showing that the drug-loaded hydrogel successfully reduced angiogenesis and proliferation of tumors. The developed hybrid thermosensitive hydrogel with improved therapeutic efficacy and sustained drug release potential was shown to be a potential technique for the local-regional therapy of HCC by intratumoral injection. Peng et al. constructed embelin-loaded thermosensitive injectable hydrogel, i.e. Embelin/PECT gel (Peng et al., 2014). Embelin/PECT gel was investigated for its cytotoxicity and antitumor activity against liver cancer (in vitro and in vivo). The results suggested that Embelin/PECT gel released the therapeutics continuously, resulting in enhanced toxicity for H22 cells upon comparison with free embelin. Within seconds of injection, the aqueous Embelin/PECT gel solution transformed into a gel, which was later being degraded in vivo. A significant antitumor effect was observed for Embelin/PECT gel at a dose of 0.5 mg per mouse comparable to the treatment of embelin solution delivered at 6 mg per mouse of the total dose. Hence, Embelin/PECT gel can be considered a novel drug candidate for advanced HCC and represents a novel drug delivery system for the liver.
In one general aspect, US 2013/0022.545 A1 temperaturesensitive hydrogel was composed of block copolymer for the liver cancer treatment via interventional injection. The synthesized hydrogel was capable of hepatic arterial catheterization and a therapeutic agent (DOX) is loaded inside the drug delivery system. The hydrogel is in the sol state at room temperature and undergoes a phase transition into the gel state inside the hepatic artery, at body temperature, thereby delaying or blocking the blood supply of the hepatic artery, and slowly releasing the DOX during the phase transition into the gel state inside the hepatic artery under the body conditions of pH 7.0-7.4 and temperature 37 C .

pH-sensitive hydrogels
pH-responsive hydrogels have widely been used in various applications, including wound healing and antimicrobial therapies, as well as tumor therapy (Qu et al., , 2019. The primary reason for developing pH-sensitive hydrogels includes the extracellular pH (pHex) of tumors (5.8 and 7.2), and endosomal or lysosomal pH is roughly 5.5, both of which are more acidic than the normal tissue pH ($7.40) (Ojugo et al., 1999). Thus, both the extracellular and intracellular endosome environments produce an acidic environment favorable to hydrogel degradation and drug release (Eckmann et al., 2014). Protonation of carboxyl groups (e.g. ionizable groups) or hydrolysis of acid-labile bonds can be attributed to pH sensitivity. pH-sensitive hydrogels have emerged as promising options to deliver drugs to tumor tissue due to their biocompatibility, biodegradability, and potential to selectively release the drug in an acidic environment. In the domain of hydrogels with pH-sensitive characteristics, pH-sensitive hydrogel theranostics and prodrugs are becoming increasingly popular. Chemotherapy medicines are conjugated with hydrogel monomers via acidlabile linkages to produce the prodrugs. They have little pharmacological activity at physiological pH ($7.40), but in an acidic environment, they transform into chemotherapeutic agents that kill tumor cells. Under acidic conditions, pH-sensitive theranostics release both pharmaceuticals and diagnostic agents concurrently from the pH-responsive hydrogel to fulfill the aim of integrating diagnosis and therapy ( Figure 5).
In addition to reducing drug accumulation in normal tissue, pH-sensitive hydrogel prodrugs improve treatment efficacy by selectively releasing drugs at acidic tumor sites, reducing systemic harmful effects. Raza et al. reported the invention of a paclitaxel delivery for tumor targeting via pHsensitive FER-8 peptide hydrogel (Raza et al., 2019). The loading ability, structure, sensitivity toward acid, rheology, drug release, morphology, cytotoxicity (in vitro), and in vivo efficacy of the pH-sensitive hydrogel system were determined in H22 tumor-bearing mice. In vitro cytotoxicity tests revealed that as compared to free pharmaceuticals, the FER-8 peptide hydrogel enhanced the accumulation of the drug in HepG2 cells and suppressed the HepG2 tumor growth efficiently. Additionally, in vivo investigations demonstrated that the FER-8 peptide hydrogel loaded with paclitaxel intensely boosted the drug content in tumor tissues and exhibited sustained retention for up to 96 hours at the tumor site. The anti-tumor studies in vivo verified HG-pH-sensitive PTX's capabilities, which enabled the drug to be released under the influence of acidic pH of tumor-bearing area, resulting in sustained drug release and increased tumor suppression. In conclusion, HG-PTX is an interesting method and prospective carrier for the efficient delivery of chemotherapeutics. Xu et al. reported the development of a biodegradable and pHresponsive DOX@ACC/PAA NP (pH 7.4-5.6) hydrogel via encapsulation of DOX in amorphous calcium carbonate (ACC) nanoparticles stabilized with poly(acrylic acid) (PAA) (Xu et al., 2019). DOX-loaded NPs are small (62 ± 10 nm) in size, have good stability in serum, have high drug encapsulation (>80%), and have high loading potential (>9%). The drug release behavior from NPs can also be adjusted to higher pH-responsive ranges (pH 7.7-6.0) by doping appropriate concentrations of Sr 2þ or Mg 2þ , allowing drug delivery to certain tissues with a less acidic condition. Lower acute toxicity of drug and tumor inhibition is proven further using zebrafish models and intracellular uptake assays, and the particles further improve drug accumulation and pharmacokinetics in mice xenograft tumors, resulting in better tumor growth suppression. The current hybrid nanocarrier may find widespread applicability in tumor therapy due to its outstanding biodegradability, biocompatibility, and tunable drug release behavior.
Qu et al. established a series of pH-sensitive polysaccharide-based self-healing injectable hydrogels for the delivery of an anticancer agent to HCC (Qu et al., 2017). By utilizing the Schiff base formation with pH-responsive behavior, we demonstrated the potential of pH-responsive hydrogels based on N-carboxyethyl chitosan (CEC) and dibenzaldehydeterminated PEGDA as a carrier for DOX delivery toward HCC therapy. They exhibited sufficient cytocompatibility to support L929 cell proliferation and were capable of releasing Dox to HepG2 cells. The degradation behavior of CEC/PEGDA hydrogels was evaluated in an acidic (PBS, pH ¼ 5.5) and physiological (PBS, pH ¼ 7.4) microenvironment. It was demonstrated unambiguously that samples in PBS with a pH of 5.5 degraded significantly more rapidly than pH of 7.4. After 48 hours, the CEC/PEGDA20 lost approximately 14% of its mass at pH 7.4 and approximately 40% of its mass at pH 5.5. Additionally, the components used to synthesize the hydrogels (CEC and PEG) are biodegradable or can be cleared by the renal tubules. Therefore, they can be completely degraded in vivo after exerting the function of a delivery vehicle. All of these findings indicate that these injectable self-healing hydrogels with pH-responsive behavior are excellent candidates for use as anticancer drug delivery carriers in the treatment of HCC.

Photosensitive hydrogels
Consider light as an external stimulus; it has been shown to increase not just hydrogel formation but also the release of loaded drugs. First, the changes occur in the hydrogel conformation upon exposure to ultraviolet, radiation, or visible light, resulting in a sol-gel transition and the production of hydrogels (e.g. free-radical polymerization, cis-trans isomerization of azobenzenes under the influence of UV light) (Lim et al., 2014;Pereira & B artolo, 2014). Second, the hydrogel is loaded with photothermal conversion-efficient material and delivered into the body. During the exposure of gel to radiation (usually NIR), light energy is converted to heat energy to disturb the structure of gel and drug release and destroy the cells associated with the tumor. This treatment is referred to as photothermal therapy currently focusing on materials having enhanced efficacy toward photothermal conversion, such as metal and nonmetallic compounds, as well as organic dyes (Huang et al., 2008;Cheng et al., 2013). Drugs with controlled release and repeatable chemo-thermal therapy have both attracted public interest (Cheng et al., 2013). Due to its capacity to permeate living tissue, NIR irradiation is commonly used in photothermal therapy as an extrinsic stimulus (Zhang et al., 2012). Finding a material with high efficiency for photothermal conversion is critical in PTT. For the first time, GhavamiNejad et al. introduced dopamine nanoparticles (DPs) into a stimuli-responsive pNIPAAm-co-pAAm hydrogel as an anticancer drug and photothermal agent (GhavamiNejad et al., 2016). When the hydrogel was illuminated with NIR light, the DP nanoparticles induced hyperthermia around tumor regions by absorbing light, thus accelerating medication release and killing tumors (Figure 6).
Hao et al. developed a degradable PEGDA hydrogel system using simple macromer formulations and visible lighttriggered thiol-acrylate photopolymerization (Hao & Lin, 2014). As a photo-sensitizer, Eosin-Y is included in this gelation system together with PEGDA, as well as a bi-functional thiol (dithiothreitol, DTT) that serves as a cross-linker and coinitiator and N-vinylpyrrolidone (NVP) as a co-monomer. Under the influence of intense visible light, gelation was accomplished utilizing a mixed-mode step-chain polymerization approach. This visible light-generated mixed-mode cross-linked hydrogel decomposed hydrolytically owing to the formation of thiol-ether-ester linkages as a result of thiolacrylate interactions. The bifunctional thiol content of the prepolymer solution and hydrolytic degradation rate was discovered to have an exponential growth relationship. Finally, we used in situ encapsulation of Huh7 cells to test the cytocompatibility of these mixed-mode cross-linked degradable hydrogels. Huh7 cells that had been encapsulated remained alive and proliferated over time, forming cell clusters. The NVP addition at a greater dose (0.3%) did not affect Huh7 cell viability, but it did result in a decrease in metabolic activity of the cell, followed by an increase in urea secretion from the encapsulated cells. Anticancer photodynamic treatment using photosensitizer chemicals integrated into hydrogels has also been reported. For instance, phthalocyanine zinc (ZnPc) was utilized in the formation of a hybrid hydrogel including PEGDA, PEG 400, and phosphotungstic acid as both a photoinitiator and a photosensitizer (Wang et al., 2013). After being exposed to NIR laser light, ZnPc becomes excited and produces singlet oxygen ( 1 O 2 ), which causes a significant drop in HeLa cell viability and proliferation rates. Hydrogel also has a high degree of biocompatibility, making it ideal for incorporating anticancer drugs into a combination or synergic therapy (Wang et al., 2013). Similar results were reported more recently using a PEGDA-based hydrogel containing methylene blue-sensitive mesoporous titanium (IV) oxide (TiO 2 ) nanocrystals produced in situ through NIR photopolymerization (Chang et al., 2019). TiO 2 was employed as a photoinitiator and photosensitizer, while methylene blue was used as a photosensitive additive to enhance TiO 2 's effects.

Ultrasound-sensitive hydrogels
Thermal and nonthermal effects of ultrasound on biological tissues are both present. Thermal effects are the conversion of acoustic energy to thermal energy, which increases tissue temperature, disruption of cell membranes, and increases vasculature permeability (Gao et al., 2005). While nonthermal effects, known as cavitation effects, are ultrasound-mediated tiny gas bubbles acting as microreactors, causing increased pressure and permeability of cell membrane, as well as the drug release received by cells (Manouras & Vamvakaki, 2017). Hydrogels with ultrasound sensitivity have typically been used in conjunction with other gene carriers or stimuliresponsive hydrogels for years (Chen & Du, 2013). They can also be used as a distinct anticancer drug carrier because of their deep permeation and visualization. Exploration of ultrasound-sensitive gels for simultaneous diagnosis and therapy is another active research area (Kumar & Han, 2017). Ultrasound has a variety of effects on the mechanism of delivery from gels. Acoustic vibrations can produce localized high heat, as evidenced by the recent use of high-intensity focused ultrasound (HIFU) in tumor treatment (Jeong et al., 2016). The release of antitumor drugs from thermosensitive hydrogels is also regulated by this thermal effect. Furthermore, ultrasound-induced cavitation greatly improves the permeability of cell membranes in ultrasound-sensitive hydrogel carriers. Wang et al. reported an in situ amidation-driven oligopeptides self-assembly and subsequent enzymatic cross-linking to prepare ternary inorganic-supramolecular-polymeric nanogels based on mesoporous silica nanoparticles (MSN) as multifunctional theranostic agent for combined ultrasound imaging and imaging-guided HIFU therapy . Supramolecular hybrid nanogels (MSN-GI) were first synthesized in situ via an amidation reaction on the surface of peptide gelators (NapFFK, NapFFK-acrylic). Following that, redox-responsive supramolecular-polymeric hybrid nanogels (MSN-GII) were synthesized via radical postpolymerization of vinyl peptide gelators with monomer and disulfide crosslinker using laccase. After therapeutic loading and guest molecules with ultrasound sensitivity, the multifunctional theranostic agent (MSN-GII@PFH&DOX) was finally constructed. This supramolecular-polymeric hybrid nanogel system can be used as a potential theranostic agent for efficient tumorresponsive drug release, enhanced ultrasound contrast visualization, and enhanced imaging-guided HIFU therapy, both in vitro and in vivo (Figure 7).

Magnetic responsive hydrogel
Aside from the most frequent stimuli for the production of sensitive hydrogels, such as temperature, pH, and light, other parameters such as a magnetic field or ionic strength can also alter the physicochemical properties of stimuli-responsive hydrogels.
Hydrogels containing iron oxide nanoparticles with paramagnetic properties are commonly used to make magneticsensitive hydrogels. As they vibrate upon exposure to the magnetic field, which results in increased local temperature by thermal ablation mechanisms, promote therapeutic efficacy. Additionally, these systems are frequently associated with thermosensitive hydrogels in which an increase in temperature results in drug release, promoting synergistic cytotoxicity via thermal and chemotherapeutics. As with NIR, this strategy exhibits spatial and temporal activity while being minimally invasive and capable of penetrating deep tissue (Kasi nski et al., 2020).
Cisplatin was combined with magnetic Fe 3 O 4 NPs (MNPs) and physically embedded into the hydrogel matrix following gelation to develop a drug-loaded magnetic nanocomposite (P(NIPAM-co-DMA)/Fe 3 O 4 ) (Salimi et al., 2018). Upon exposure to an external magnetic field, the synthesized nanocomposite dispersion was found to be transparent, demonstrating the super magnetic behavior of the nanocomposite. The highest release behavior was observed at pH 5.8, 40 C with augmented efficacy in HepG2 cells owing to improved and targeted delivery. In another work, Fe 3 O 4 NPs and CTS were successfully utilized for the synthesis of methotrexate (MTX)encapsulated magnetic-/pH-responsive hydrogel beads through a one-step gelation process (Wu et al., 2016). Additionally, the hydrogel beads were found to be extremely sensitive to pH changes as well as having an extremely homogeneous porous structure with super magnetic potential. The hydrogel beads released the encapsulated MTX at pH 4.0 HepG2 cell proliferation was effectively inhibited by MTX-encapsulated magnetic hydrogel beads in the WST-1 test. All of these findings suggest that pH-sensitive magnetic CTS hydrogel beads encapsulated with MTX may be a promising vehicle for targeted cancer treatment. Yan et al. reported the in situ formed magnetic hydrogel using magnetite decorated reduced graphene oxide nanosheets (denoted as FG) and NDP hydrogel with strong adhesion in wet conditions, promising thermal responsiveness for use in biomedical applications, high magnetic hyperthermia, and biocompatibility, leading to efficient HCC multidisciplinary treatment including postoperative treatment and transarterial embolization therapy (Yan et al., 2022). The hydrogel's ability to reduce postoperative recurrence was demonstrated in vivo. Further evidence of the thermal-responsive hydrogel's hemostatic properties was provided by studies using the liver scratch model and resection of a liver tumor. CT imaging showed the complete embolization of the arterial vessels of a rabbit liver tumor during a vascular intervention operation, suggesting that it could be used as a multidisciplinary responsive material to an external magnetic field for the treatment of HCC. Qian et al. synthesized an injectable magnetic hydrogel based on iron oxide nanocubes (IONCs) and silk fibroin (Qian et al., 2020). Using ultrasound-guided interventional treatment, it was discovered that the manufactured hydrogel may be injected into tumors, particularly rabbit HCC in deeper regions. This hydrogel, unlike photothermal agents, has remote hyperthermia capability in an alternate magnetic field, which resulted in effective magnetic hyperthermia of deep tumors including a subcutaneously implanted tumor model in Balb/c mice after covering it with fresh pork tissue and an orthotopic liver tumor transplantation in rabbit. Additionally, by incorporating IONCs in a silk fibroin hydrogel, undesirable thermal damage can be avoided, as compared to direct delivery of monodispersed magnetic nanoparticles (Figure 8) ( Table 2).

Active targeting
Active targeting can be used to deliver therapeutic drugs to tumors with high specificity and efficiency using various ligands that serve as a targeting moiety . It is possible to incorporate active targeting into nanomedicines because of their large surface area. Active targeting may be able to overcome passive targeting's limitations (Yan et al., 2015). It is possible to include active targeting capabilities in NPs because of their large surface area and sophisticated chemical ligation procedures. This targeting technique is based on ligand interactions with receptors or antigens that are overexpressed on the target cells resulting in receptor-mediated endocytosis and the selective delivery of NPs (Rosenblum et al., 2018). Numerous nanomedicines based on an active targeting approach have been studied for liver cancer therapy, with several demonstrating increased anticancer activity while avoiding side effects (Varshosaz & Farzan, 2015;Lu et al., 2018). Currently, the most often employed ligands in liver cancer therapy include galactose, glycyrrhetinic acid, folate, and short peptides, as well as macromolecular ligands such as transferrin (Tf), aptamers, antibodies. Chen et al. replaced GA with naphthylacetic acid to form a supramolecular pro-gelator of curcumin modified by GA (GA-Cur) and a control compound Nap-Cur (Nap) . Both compounds were water-soluble and could form gels in vitro via the reduction of disulfide bond induced by glutathione (GSH). In buffer solutions, both gels were capable to give extended-release of Cur. We also used an MTT assay to determine the pro-gelators cytotoxicity to HepG2 cells, as well as LC-MS and fluorescence microscopy to determine their cellular uptake behaviors. As GA receptor overexpressed on the cancer cells of the liver, our GA-Cur pro-gelator demonstrated improved inhibition and cellular uptake through tumor cells of the liver compared to Nap-Cur. Hence, the GA-Cur has the potential to considerably inhibit HepG2 cell growth and found to be a novel nanosystem for the treatment of liver tumors. Furthermore, selfassembled hydrogel nanoparticles were developed by replacing the carboxymethylated (CM)-curdlan with sulfonylurea (SU) which was then functionalized with lactobionic acid for enhanced interaction with HepG2 cells. Ligand-receptor interactions with fluorescence-labeled LBA/CM-curdlan/SU hydrogel nanoparticles strongly illuminated HepG2. Other control cases did not exhibit luminescence. The authors conclude that hydrogel nanoparticles based on LBA/CM-curdlan/ SU can be served as an effective approach for cancer therapy of the liver, owing to the immunostimulatory properties of CM-curdlan, the specific interactions mediated by the ligandreceptor, and the controlled release of the anticancer drug (Na et al., 2000).

Combination therapy
The development of a combination therapy-based platform is critical for enhanced antitumor efficacy and decreased recurrence of the tumor, as it enables the selective delivery of heat and anticancer drugs to the tumor site in a controlled manner. To achieve improved local tumor control, an injectable nanocomposite hydrogel was incorporated with PEGylated gold nanorods (GNRs) and CTS polymeric micelles loaded with PTX (PTX-M) were developed . The thermosensitive hydrogel matrix can deliver and immobilize GNRs and PTX-M to the tumor after intratumoral injection. By using laser irradiation, the photothermal damage caused by the GNR is restricted to the tumor, while the healthy cells remained protected. PTX-M and the sustained drug release from the co-delivered PTX-M work together to destroy residual tumor cells. In Heps-bearing mice, this combination therapy shows superior benefits in suppressing tumor recurrence and extending survival as compared to photothermal therapy alone. Zhang et al. developed a sustained and programmed PCL-PEG-PCL thermosensitive hydrogel-based drug delivery system that was combined with multiwalled carbon nanotubes (CNTs) using rhodamine B (RB) and doxorubicin (DOX) as model drugs (Wei et al., 2018). In contrast to other dual drug delivery systems, in vivo fluorescence imaging can track co-loaded dual drug delivery systems in real-time due to their suitable fluorescence. Carbon nanotubes loaded with DOX were combined with hydrogels to develop a hydrogel-CNT system that can deliver drugs in a controlled manner. Nude mice were used as a  Qian et al. (2020) model to track the real-time delivery of two drugs via florescence imaging, which was programmed to be delivered sequentially. Using two drugs in combination, the CNTs/ hydrogel system has the potential to be used as a delivery vehicle with controlled released. The unique fluorescence signals of the two drugs can be used to track their delivery and distribution in the drug delivery system. On-demand combination chemotherapy may be guided by fluorescence imaging tracking in vivo. Jin et al. synthesized hollow gold nanoshells (HAuNS) and genetically engineered polypeptide-based injectable hydrogel for chemo-photothermal therapy of HepG2 tumor (Jin et al., 2019). We began by layer-by-layer coating with DOX and PC10A to develop a drug-loaded hybrid PC 10 A/DOX/ HAuNS nanogel which were dissolved in PC 10 A hydrogel to develop injectable PC 10 A/DOX/HAuNS hydrogel with a variety of excellent properties. HAuNS and PC 10 A/DOX/HAuNS hydrogels were combined to release the drug DOX sequentially, with one part of the drug absorbed on the HAuNS and the other in the PC 10 A hydrogel. An impressively enhanced tumor inhibition was observed in both cell culture and mice models when the combined therapy of chemotherapy and photothermal therapy was used instead of either therapy alone. Due to this, the PC 10 A/DOX/HAuNS hydrogel has the potential to offer a new strategy for chemo-photothermal therapy (Figure 9). Peng et al. synthesized a chemotherapeutic drug (liposomal DOX) and therapeutic radionuclide ( 188 Re-Tin colloid) containing thermosensitive hydrogel (Peng et al., 2013). Temperature changes cause a sol-gel phase transition in the thermosensitive PCL-PEG-PCL copolymer, which quickly forms a gel at body temperature while remaining liquid at room temperature. The hydrogel was slow to release radionuclide and DOX, and the system remained stable for almost 10 days. After intra-tumor injection of Lipo-Dox/ 188 Re-Tin hydrogel in HCC bearing mice, the tumor's retention, distribution, and therapeutic effect were investigated. 188Re-Tin loaded hydrogel had a significantly longer residence time in the tumor than Na 188Re perrhenate (Na 188ReO4). When the hydrogel undergoes thermal transition, the radionuclide 188 Re perrhenate ( 188 ReO4) quickly diffused from the tumor.
Compared to treatment with either 188Re-Tin hydrogel or Lipo-Dox hydrogel, treatment with Lipo-Dox/ 188 Re-Tin hydrogel significantly reduced tumor growth (up to 80% regression of well-established tumors on day 32). It is possible that this biodegradable injectable hydrogel would therefore allow Figure 9. (a) In this schematic, we show the steps involved in developing PC 10 A/DOX/HAuNS hydrogels and nanoparticles, as well as the steps involved in dissolving the nanoparticles in the PC10A hydrogel. (b) The sequential drug release of PC 10 A/DOX/HAuNS hydrogels was used for long-term chemotherapy and photothermal therapy in vivo (Jin et al., 2019).
for more precise localization of radiotherapy and chemotherapy for the treatment of HCC (Table 3).

Limitations of hydrogel-based drug delivery systems in cancer treatment
Despite their numerous advantages, hydrogels do have a few limitations. Several hydrogels cannot be used in loadbearing applications due to their low tensile strength. These hydrogels prematurely dissolve or flow away from a designated site (Bai et al., 2020). This constraint may be more relevant in many conventional drug delivery applications (e.g. subcutaneous injection, in situ injection, and intratumoral injection). Perhaps a more significant concern is about the drug delivery capabilities of hydrogels. Drug loading into hydrogels may be limited in terms of amount and uniformity, particularly for hydrophobic drugs. The large pore diameters and high-water content of most hydrogels result in the rapid release of payloads, or burst release (Tsirigotis-Maniecka et al., 2021). The ease of application is also a significant concern. Some hydrogels can be injected, but many cannot be, so they have to be implanted through surgery. Due to these limitations, the use of hydrogel-based therapies in clinical applications may be restricted (Table 4). Furthermore, hydrogels prospective therapeutic application in cancer treatment is still in its inception. There are several reasons behind this (Cao et al., 2019). The tissue penetration depth of NIR is limited to 3 mm when employing 810 nm NIR of less than 1 W, limiting its use in treating subcutaneous tumors or skin cancer (Nakamura et al., 2019). Colorectal cancer and ovarian cancer are two examples of deep tumors in the human body that appear to be difficult to treat with this method. Photo-crosslinking hydrogels for shallow visible light penetration have the same issue. Even though many studies use subcutaneous tumors as an in vivo model, there are often important and complex anatomical structures (e.g. lymphatic systems, veins, arteries, and nerves) located around the tumor that can be eroded by carcinoma tissue and must be taken into account when developing a treatment plan for cancer (Nagakawa et al., 2020). There is also a lack of hydrogel-related research on degradation and metabolism, immunological response, and biodistribution in the body for patients of different sexes and ages. As a result, hydrogel-based cancer treatment has a long way to go before it can be practiced in clinics.

Conclusions and prospects
Hydrogel-based drug delivery systems can be used to treat many diseases, including cancer. Hydrogels water-loving nature and capability to swell and shrink under the influence of environmental signs or just the water presence make them appealing for drug delivery. They are highly porous, and the polymers used to make them can further be crosslinked to varying degrees. With a flexible physical structure, hydrogels can be used for more than just targeted drug delivery. They are used in tissue engineering, contact lenses, wound care, and hygiene. Hydrogels have made tremendous strides in targeted and localized drug delivery. They are modified with polymers of various types and targeting ligands, giving them unique drug delivery properties. A perfect hydrogel material should have a high biodegradability and not produce any toxic substances. Flexible stimulus responsiveness, and even multi-stimulus responsiveness, as well as high drug loading efficiency, are all desirable properties of an ideal hydrogel-based drug delivery system. In the context of cancer chemotherapy, in situ hydrogels not only act as loading drugs and drug carriers for unstable and poorly soluble drugs but also act as a localized depot for the subsequent release of multiple drugs. Nanogels have better biocompatibility and solubility than other nanoparticles and can avoid mononuclear phagocyte system clearance after chemical modification. Nanogels have a larger surface area and thus respond faster to a stimulus after in situ injections. Despite this, there are still challenges in translating experimental findings into clinical practice. As a result of the difficulty in detecting nucleic acids and therapeutic proteins, the metabolism and release rate of the hydrogels remain ambiguous in vivo. Also, while animal models can assess short-term biocompatibility, long-term biocompatibility is not guaranteed, specifically for the synthesized materials. Hence, rigorous evaluations of newly emerged materials should be considered. Comprehensive research is required to advance hydrogel-based delivery vehicles into clinical trials. The trend points to the use of precisely tunable and highly controlled hydrogels in the future. Interdisciplinary researchers should work together to make hydrogels a safe and practical chemotherapy approach.

Disclosure statement
No potential conflict of interest was reported by the author(s).